Laminar construct for tissue-engineered dermal equivalent

ABSTRACT

Compositions and methods for creating a laminar construct for tissue-engineered dermal equivalent are provided. One composition provided herein comprises a hydrogel matrix comprising two or more hydrogels layers and a population of stem cells. Associated methods are also provided.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a divisional of U.S. patent application Ser.No. 12/870,128 filed Aug. 27, 2010, which claims the benefit of U.S.provisional patent application Ser. No. 61/237,868 filed on Aug. 28,2009.

STATEMENT OF GOVERNMENT INTEREST

This invention was made with support under Grant Number W81XWH-08-C-0062awarded by the US Army Medical Research and Materiel Command. Thegovernment has certain rights in the invention.

BACKGROUND

Skin grafts are often necessary for the treatment of severe,full-thickness burns, non-healing skin ulcers and other surgicaloperations where there is loss of skin or a need for skin coverage ofsoft tissue. The graft procedure involves placing a layer of healthyskin on the wound site. The graft serves to close the wound, protectingthe underlying tissue to facilitate healing. Two main classifications ofskin graft surgery, autograft and allograft, depend on the source of thedonor tissue. In an autograft operation, the skin graft is harvestedfrom a different location on the patient. In an allograft operation, thegraft is harvested from an external source such as another donor (e.g.,cadaver) or is prepared artificially (e.g., dermal equivalent).

Previous work done in the field of tissue engineering has produced skingrafts that may be used in surgery. Generally, the tissue graft may beproduced by seeding a collagen matrix or other biocompatible materialwith the appropriate cells to create the desired culture. As the cellsproliferate, the matrix degrades and is eventually replaced by a layerof healthy tissue. This layer of tissue or the matrix seeded with cellsmay be used in skin graft surgery.

Recent advances in tissue engineering based wound dressings haveresulted in the emergence of a range of dermal, epidermal and evencomplete skin equivalents. Advances in cellular biology and knowledge inwound healing and growth factors have provided a wide variety of choicesto attack the problem of the complex wound. Continued research and newdevelopments have improved the level of care in the field of complexburn wound care and has resulted in the availability of epidermal,dermal and total skin substitutes.

For example, Epicel, a cultured epidermal autograft (CEA), is one of theearly tissue engineered products. It is an epidermis cultured in vitroand not a true skin equivalent which may limit its range of potentialuses. CEA requires several weeks to produce, has a low rate of grafttake, is very fragile, is susceptible to infection, and is not suitablefor use without a dermal layer. To address the above problems,composites consisting of dermal equivalents in combination withepidermal components were developed. A typical engineered skinsubstitute (ESS) is composed of an epidermal substitute of autologouskeratinocytes, attached to a dermal analogue of collagen orcollagen-glycosaminoglycan combination populated with autologousfibroblasts. Following in vitro culture prior to grafting, ESSdemonstrates morphogenesis similar to native human skin.

However, current efforts to produce suitable dermal equivalents arecomplicated by the multiple layers and corresponding functions that mustbe present. For example, the external layer must be capable of closingthe wound and providing protection to the underlying tissue. Internallayers must be conducive to the formation of blood vessels andcirculation. The state-of-the-art techniques in tissue engineered skinrely on the sequential culture of dermal fibroblasts and keratinocyteson a collagen matrix. The culture process relies on a relatively longculture time to increase cell numbers within the construct before asuitable dermal equivalent has been produced.

SUMMARY

The present disclosure generally relates to laminar constructs and morespecifically, to laminar constructs for tissue-engineered dermalequivalents.

In one embodiment, the present disclosure provides a laminar constructcomprising a hydrogel matrix comprising at least a first hydrogel layerand a second hydrogel layer, and a plurality of mesenchymal stem cells.

In another embodiment, the present disclosure provides a method ofcreating a laminar construct comprising: providing a hydrogel matrixcomprising at least a first hydrogel layer and a second hydrogel layer,and introducing a plurality of mesenchymal stem cells to the hydrogelmatrix.

In yet another embodiment, the present disclosure provides a methodcomprising preparing a dermal equivalent for an allograft operation fora patient, wherein the dermal equivalent comprises a hydrogel matrixcomprising at least a first hydrogel layer and a second hydrogel layer,and a plurality of mesenchymal stem cells.

The features and advantages of the present invention will be readilyapparent to those skilled in the art. While numerous changes may be madeby those skilled in the art, such changes are within the spirit of theinvention.

DRAWINGS

The patent or application file contains at least one drawing executed incolor. Copies of this patent or patent application publication withcolor drawing(s) will be provided by the Office upon request and paymentof the necessary fee.

A more complete understanding of this disclosure may be acquired byreferring to the following description taken in combination with theaccompanying figures in which:

FIG. 1 illustrates the creation of a bilayer dermal construct, accordingto one embodiment.

FIG. 2 is a schematic of a layered construct according to one embodimentwhich could provide both the vascular as well as dermal fibroblastcomponent for treatment of wounds.

FIG. 3 illustrates the creation of a laminar skin equivalent, accordingto one embodiment.

FIGS. 4A and 4B depict immunohistochemical staining against CD31 andvWF, respectively, of human MSCs embedded in PEGylated fibrin after 7days. The images use nuclear counterstain with DAPI (20×). FIG. 4Cdepicts PCR showing that entrapped MSCs highly expressed VEGF and vWF(lane 2 and 5), expressed CD31 (lane 6), but did not express CD 34 (lane4). FIG. 4D depicts a gel plug assay using 1 ml preformed gel plugsafter a 7 day subcutaneous implant. The left image is fibrin gel onlywhile the right is PEGylated fibrin. The arrow denotes blood vessel inthe gel interior.

FIG. 5 depicts the differentiation of ASC into vascular like structuresin PEGylated fibrin.

FIG. 6 depicts the proliferation timecourse of ASC in PEGylated fibrin.

FIGS. 7A-7L depict Confocal Z-stacked images of tube-like structuresformed by ASC in PEGylated fibrin gel. ASC when seeded in PEGylatedfibrin exhibit an endothelial phenotype expressing both von Willebrandfactor (B) and CD31 (C). FIG. 7D shows the merged image of 7B and 7Cstained with Hoeschst (D) for nuclei. The formed tubes were positive forboth pericyte specific markers NG2 (G) and α-SMA (FIG. 7K) and theendothelial cell specific marker von Willebrand factor (7F and 7J).FIGS. 7H and 7L shows von Willebrand factor and Hoeschst (7E and 7I)merged with NG2 and α-SMA, respectively.

FIG. 8 depicts a schematic representation of the differentiationstrategy of ASC. Light micrographs are shown that were taken at variousdays of ASC differentiated to epithelial like cells. Control (Top),differentiated ASC (bottom).

FIG. 9 depicts isolated ASC that were analyzed by immunohistochemistryand expressed p63.

FIG. 10 depicts cells that were subjected to keratinocytedifferentiation and expressed a deep granulated appearance.

FIG. 11 depicts the staining for Pan-cytokeratin and cytokeratin 18 ofcells cultured in complete media (GFs).

FIGS. 12A and 12B depict sections showing differentiated ASC to organizelike an epithelial layer over collagen matrix (A; col-collagen).Immunofluorescence image of section showing positive for pan cytokeratin(B) and krt 10 (C) (Alexa fluor 594 and Hoeschst overlay).

FIG. 13 depicts the immunocytochemical analysis of ASC isolated fromrats. Photomicrographs are of markers expressed in third passage ASC.Figures in each panel indicate the specific cell surface marker. Allantibodies, except Stro-1, are FITC-labeled primary antibodies. Stro-1is identified using isotype matched FITC-labeled rat IgM. Allphotomicrographs at ×20 magnification.

FIG. 14 depicts light microscopic images of differentiation time-courseof ASC into vascular like structures. Cells began to form vasculartube-like networks in the PEGylated fibrin gel in the absence ofadditional soluble cytokines The amount of network formation was relatedto the initial cell density. (Scale bar=100 μm)

FIG. 15 depicts endothelial and pericyte specific markers expressed bythe differentiated ASC in PEGylated fibrin gels. Expression levels ofendothelial cell specific markers (CD31, von Willebrand factor) andpericyte specific markers (NG2 and PDGFRβ) were analyzed using Real TimePolymerase Chain Reaction (RT-PCR). There was significant increase inendothelial cell specific markers; CD31 (25 fold) and vWF (42 fold) incomparison to pericyte markers; NG2 (6 fold) and PDGFRβ (9 fold) by day11.

FIGS. 16A-16F are images depicting ASC released from chitosanmicrospheres in vitro in PEGylated fibrin and collagen gels. Phasecontrast images of ASC migrated from chitosan microspheres into collagen(A, B and C) and PEGylated fibrin (D, E and F). ASC that have migratedfrom CSM attached to the PEGylated fibrin shows classical sprouting (A,day 2) followed by differentiating into tube-like structures (B, day 5).Over the time course of differentiation, they migrate into the gelforming a dense multicellular network (Day 8, C). ASC released from theCSM into collagen were more spindle in appearance (Day 2, D) whichdeveloped filopodias (Day 6 E). Over time they formed more elongatedmorphological structures stretching along fibril assemblies resemblingcells that are associated with stromal tissues.

FIGS. 17A-17F are images depicting Qdot 565 labeled ASC tracked aftermigration from chitosan microspheres after Day 6 into PEGylated fibrinand collagen gels. Epifluorescent images of Qdot 565 labeled ASC trackedafter migration from the CSM into PEGylated fibrin (A-C) and collagen(D-F) after 6 days. ASC released from chitosan microspheres into bothPEGylated fibrin and collagen could be tracked (A and D) over 6 days.Cells forming tubes-like structures (B) in PEGylated fibrin and striatedmorphologies (E) were colocalized with Qdot 565 (C and F).

FIGS. 18A-18H are images depicting the bidirectional differentiation ofASC in the PEGylated fibrin—(ASC-CSM)—collagen gel constructs. ASCloaded in CSM exhibited matrix driven phenotypic changes into afibroblast-like morphology in the collagen layer (A, C, E and G) and atube-like morphology in the PEGylated fibrin layer (B, D, F and H)simultaneously. ASC started to migrate into both the gels on Day 3 (Aand B) and proliferated as a fibroblast-like phenotype in collagen (C)and tube-like sprouts (D) in PEGylated fibrin on day 5. By day 7 thecollagen layer showed an increase in fibroblast-like cells (E) whicheventually populated the gels by day 11 (G). In the PEGylated fibrinlayer the sprouts started to form long networks by day 7 (F) whichformed complex networks by day 11 (H).

While the present disclosure is susceptible to various modifications andalternative forms, specific example embodiments have been shown in thefigures and are herein described in more detail. It should beunderstood, however, that the description of specific exampleembodiments is not intended to limit the invention to the particularforms disclosed, but on the contrary, this disclosure is to cover allmodifications and equivalents as defined by the appended claims.

DESCRIPTION

The present invention discloses a laminar construct fortissue-engineered dermal equivalents. By applying the teachings of thisdisclosure, a person of ordinary skill in the art would be able tocreate a multi-layered tissue culture from a single source of stemcells. The present teachings allow for the formation of both bloodvessels and dermal connective tissue from a uniform cell population thatmay be seeded and spontaneously assemble into the desired layers withoutthe need for long culture times that are necessary when multiple layersare cultured sequentially. This tissue culture is useful as a dermalequivalent or tissue-engineered skin.

In one embodiment, a laminar construct of the present disclosurecomprises a hydrogel matrix and a population of mesenchymal stem cells(MSC). Stem cells are unique among cells that may be cultured becausethey are not constrained to a particular cell type. Rather, stem cellsfrom a single source are capable of differentiating into a variety ofdistinct cell types depending on their environment and other externalfactors. External factors may include soluble signals, insoluble ormatrix molecules or other cell types. Soluble signals include, but arenot limited to, growth factors, hormones and bioactive small molecules.Matrix molecules include, but are not limited to, fibrous proteins suchas collagen and elastin, adhesion proteins such as fibronectin andlaminin as well as glycosaminoglycans such as hyaluronic acid orchondroitin sulfate either alone or complexed as a proteoglycan. Infact, a single source of stem cells may differentiate into multipletypes of tissue depending upon the properties of the hydrogel matrixthat surround an individual stem cell. In certain embodiments, thehydrogel matrix may be engineered to control cell differentiation in theabsence of growth factor supplementation of culture media.

The population of stem cells may be sourced from multiple locations inthe human body including, but not limited to, fat, bone marrow, bloodand muscle. Mesenchymal stem cells derived from adipose tissues (ASC)differentiate into multiple phenotypes including adipose, muscle, bone,neuronal, endothelial, hepatocyte and epithelial-like cells. Adiposetissue is an attractive in vivo cellular source of autologous stem cellsfor regenerative therapies for several reasons. Adipose-derived stemcells may be easily isolated from the stromal vasculature ofsubcutaneous adipose tissue by liposuction with a minimally invasiveprocedure and the excised adipose contains 100 to 1000 times morepluripotent cells per cubic centimeter than bone marrow. In certainembodiments, the population of stem cells may be sourced from thepatient or a donor. The stem cells may be harvested by any method ortechnique known in the art.

The laminar construct also comprises a hydrogel matrix. In someembodiments, the hydrogel matrix comprises two or more hydrogel layers.One possible hydrogel layer may comprise a material that encourages stemcell differentiation towards blood vessel cells. Examples of suchhydrogel layers include, but are not limited to, hydrogels comprisingfibrin, PEGylated fibrin, hyaluronic acid and soluble degradationproducts thereof. Hydrogels suitable for use in the present disclosuremay also comprise matrix molecules along with soluble signals known toencourage blood vessel in-growth during inflammation and wound healing.PEGylated fibrin exhibits several unique features of both synthetichydrogels and natural materials. First, the presence of PEG provides ahighly hydrated (>90% water) moist environment for managing exudate. Thepresence of fibrin confers biodegradability to the material; however,PEGylated fibrin is potentially more stable in vitro than fibrin alone.Finally, the inherent biologic activity of fibrin stimulates tissue andblood vessel in-growth.

Additionally, a layer of the hydrogel matrix may comprise a materialthat encourages stem cell differentiation towards dermal fibroblasts.This type of material includes, but is not limited to, types I, II, III,IV and V collagen; adhesion proteins such as fibronectin, tenascin andvitronectin; glycosaminoglycans such as chondroitin sulfate, heparansulfate and hyaluronic acid as well as provisional matrix proteinsincluding fibrin-based materials or combinations thereof.

The hydrogel matrix may be created by any method or technique known inthe art. For example, PEGylated fibrin may be created by modifyingfibrinogen (Fgn) with the benzotriazole carbonate derivative ofpolyethylene glycol to create secondary crosslinking Specifically, aderivatized polyethylene glycol (PEG) has end groups that may react withpeptide side chains such as amine, hydroxyl, carboxyl or thiolfunctionalities. The derivatized PEG is typically a carbonate,N-hydroxysuccinimide ester, epoxide, or tresylate group. The reaction ofderivatized PEG with proteins may be performed under relatively mildconditions at room or body temperature in aqueous solution at pH valuestypically between 6.0 and 8.0. Reaction times are dependent on thereactivity of the PEG end groups and may proceed for between 5 minutesto several hours. Potential amine-reactive PEG derivatives include, butare not limited to, benzotriazole carbonate PEG, succinimidylmethylbutonoate PEG, succinimidyl propionate PEG, nitrophenyl carbonatePEG, succinimidyl carbonate PEG, succinimidyl succinate PEG,succinimidyl glutarate PEG, and succinimidyl valerate PEG. In apreferred embodiment, an end-group hydrolysis rate of about 20 minutesis used.

Once sourced, the stem cells of the present disclosure may be combinedwith the hydrogel matrix in a variety of ways. In one embodiment, thesestem cells may be sandwiched between the two or more hydrogel layers. Inanother embodiment, the stem cells may be seeded uniformly within thehydrogel layers prior to gellation of the matrix. The stem cells may beseeded from suspension or following culture on microcarrier beads, suchas chitosan microspheres. In a preferred embodiment, the cells areseeded on microcarriers and “sandwiched” between two hydrogel layers asshown in FIGS. 1 and 2.

The present disclosure presents a number of advantages over existingtechniques. For example, if the stem cells are sourced from anindividual patient, the process results in an autograft with fewerimmune complications. Simpler production results from inducing the cellsto differentiate towards different cell types, including but not limitedto vascular and dermal cells, via properties of the hydrogel matrixrather than the culture conditions. Additionally, the present disclosureprovides for the formation of blood vessels within the structure whichmay increase the viability of the construct. One limitation, the lack ofepidermal (keratinocyte) cell population, may be overcome throughin-growth or via split-thickness grafts.

To facilitate a better understanding of the present invention, thefollowing examples of certain aspects of some embodiments are given. Inno way should the following examples be read to limit, or define, theentire scope of the invention.

Example 1

From previous work, it has been demonstrated that MSCs by themselvescannot differentiate into cells expressing EC phenotype withoutinduction by the appropriate cytokines Endothelial cell tubes inMatrigel™ typically disappear within a few hours. However, in PEGylatedfibrin gel, MSCs maintained vascular tube-like networks until the geldegraded, approximately 7-10 days later. Murine, porcine and rat MSCsmay also be capable of forming tubes within the PEGylated fibrin gels.Controls of unreactive PEG mixed with fibrinogen demonstrate CD31 andvWF negative phenotype. In addition to the effects that can be realizedfrom embedded MSCs in PEGylated fibrin gels, the gels alone are able tosupport capillary ingrowth in a subcutaneous implantation in Lewis rats.FIGS. 4A and 4B illustrate the results of embedding human MSCs inPEGylated fibrin. FIG. 4C depicts PCR showing that entrapped MSCs highlyexpressed VEGF and vWF (lane 2 and 5), expressed CD31 (lane 6), but didnot express CD 34 (lane 4). FIG. 4D compares fibrin gels alone after a 7day gel plug implantation relative to the PEGylated fibrin gels. ThePEGylated fibrin clearly supports extensive capillary in-growth.

Example 2

Having seen that PEGylated fibrin gel can induce robust tube-likedifferentiation of mesenchymal stem cells, it was further investigatedwhether adipose derived stem cells (ASC) could differentiate into atypical vascular network. Advantages of using ASC are that they can beeasily isolated from the stromal vasculature of subcutaneous adiposetissue by liposuction with minimally invasive procedures and the excisedadipose is enriched in progenitor cells relative to bone marrow. Recentstudies provide evidence that infused ASC in vivo are non-immunogeniceven when used in immunocompetent animals. Adipose derived stem cellswhen delivered to tissue defects elicit tissue regeneration by paracrineactivation of host cells through secretion of growth factors, autocrinesignaling or through direct cell-cell interactions.

Preliminary investigations show that ASC were able to form robust tubelike structures as shown in FIG. 5. Within 7 days ASC were able to formdense vascular structure within PEGylated fibrin matrix, with initialseeding density of 50000 cell/ml of PEGylated solution, and showedalmost a linear increase in proliferation. See FIG. 6. Certainendothelial cell specific markers including vWF and CD 31 werepositively identified. The amount of vascularization was related to theinitial cell number plating density. Accordingly, cell proliferation andviability increased with increasing cell seeding density, as shown inFIG. 6. Additional preliminary data indicate that, in the case ofembedded ASC, cells do exhibit positive staining for pericyte markerssuch as smooth muscle alpha-actin (sma-actin) and NG-2 (chondroitinsulfate proteoglycan). Sees FIGS. 7A-7L. This early result providesevidence for the existence of a differentiated cell occupying a pericytefate during ASC culture in PEGylated fibrin. In addition they alsoexhibited endothelial specific markers, including vWF and CD31.

Example 3

ASCs may be differentiated into epithelial lineages and used for theproduction of a skin substitute. Previous studies show that mesenchymalstem cells infiltrate into a wound site and transdifferentiate intoendothelial, and stromal like populations. This example describes amethod to differentiate adipose derived stem cells into epithelial likecells and analyzed the expression of lineage specific cytokeratinmarkers.

Adipose derived stem cells were isolated using methods known in the art.The pelleted stromal cells were plated and attached cells propagated.Passage 3 cells were characterized for their immunophenotype andsubjected to differentiation into epithelial cells. The differentiationmedia consisted of low glucose DMEM and either one or more growthfactors including: keratinocyte growth factor (KGF), epidermal growthfactor (EGF), hepatocyte growth factor (HGF), insulin like growth factor(IGF) with or without all trans retinoic acid (ATRA) and with or withoutperoxisome proliferator-activated receptor (PPAR) agonists such asfenofibrate. FIG. 8 is a schematic representation of differentiationstrategy adopted in this procedure. The cultures were monitored fordifferentiation and harvested for analysis at day 12.

The morphology of the ASC undergoing differentiation into keratinocyteswas observed by light microscopy and differentiated cells were analyzedusing immunohistochemistry to monitor the differentiation intoepithelial cells using standard protocols. (See FIG. 8). The isolatedASC expressed standard stem cell markers (e.g., Strol-1, CD71, CD54,Sca-1). They also expressed p63, as shown in FIG. 9, a nucleartranscription factor that has been shown to be essential for thecommitment of a simple ectoderm to epidermal lineages, maintenance, anddifferentiation. Cells subjected to keratinocyte differentiation mediaexhibited the squamous structure with deep granulated appearance by day12, as shown in FIG. 10, while cells that were in control media did notdifferentiate. Cells cultured in complete media (GFs) differentiated andstained positive for Pan-cytokeratin and cytokeratin 18, intermediatefilament proteins responsible for the structural integrity of epithelialcells. See FIG. 11.

The differentiation ability of adipose derived stem cells using acombination of growth factors and retinoic acid provides a system fordevelopment of epidermal equivalents using appropriate biomaterialconstructs.

Example 4 Materials and Methods Isolation of Adipose Derived Stem Cells

Rat adipose mesenchymal stem cells (ASC) were isolated from perirenaland epididymal adipose tissue using methods known in the art. Perirenaland epididymal adipose tissue was collected and washed with sterileHanks buffered balance solution (HBBS) containing 1% bovine serumalbumin (BSA). The tissue was minced, transferred into 25 ml of HBBS andcentrifuged (500×g at room temperature for 10 min). The free floatingadipose tissue layer was collected, transferred to 25 ml of HBSScontaining 1% Fetal Bovine serum (FBS) and 200 U/ml of collagenase typeII (Sigma-Aldrich, St. Louis, Mo.) for 45 minutes at 37° C. in anorbital shaker. The digested tissue was then filtered through 100 μm and70 μm nylon mesh filter, centrifuged for 10 minutes, 500×g at roomtemperature, washed twice with sterile HBBS. The cell pellet wasre-suspended in growth media (MesenPRO RS™ Basal Medium, supplementedwith MesenPRO RS™ Growth Supplement, antibiotic-antimycotic (100 U/ml ofPenicillin G, 100 μg/ml streptomycin sulfate and 0.25 μg/ml AmphotericinB) and 2 mM L-Glutamine (GIBCO, Invitrogen, Carlsbad, Calif.). Cellswere cultured on T75 flasks (BD Falcon, Franklin Lakes, N.J.) andmaintained in a 5% CO2 humidified incubator at 37° C. Passage 2-4 ASCwere used for all experiments.

Immuncytochemistry of Stem Cell Surface Markers

ASC were incubated on a 2-well chambered slide (Nalge Nunc, LabTek®chamber slide, Noperville, Ill.) for 48 hours. The cells were washedtwice with sterile HBSS, fixed with 4% paraformaldehyde for 15 minutes.Fc receptor mediated blocking sites were blocked by incubating the cellsfor 20 minutes with (1 μg/104 cells) of BD Fc Block™ Solution (BDBioscience, San Jose, Calif.) or non-permeant blocking solutioncontaining 5% donkey serum (Sigma, St. Louis, Mo.) in HBSS. Stem cellsurface markers were identified by incubating ASC overnight, 4° C., with10 μg of fluorescein isothiocytnate (FITC) conjugated anti-mousemonoclonal antibodies against CD54 (ICAM-1), CD71 (transferrinreceptor), CD 49d (integrin α4) and CD90 (Thy-1 glycoprotein) (BDBioscience, San Jose, Calif.). To observe STRO-1 (R&D Systems,Minneapolis, Minn.) expression, cells were fixed with 4%paraformaldehyde for 15 minutes, washed twice with phosphate-bufferedsaline (PBS), blocked with 2% serum and incubated overnight at 4° C.with 10 μg of STRO-1. The cells were washed twice with PBS and incubated45 minutes at 4° C. with 5 μg/ml of FITC labeled anti-mouse IgMsecondary reagent (R&D Systems, Minneapolis, Minn.). Non-specificfluorescence was determined using ASC incubated with FITC labeled Igclass secondary antibody reagents.

Preparation of ASC Seeded PEGylated Fibrin Gel

PEGylated fibrinogen was prepared as per our previous procedure withslight modification. BTC-PEG-BTC (benztriazole modified polyethyleneglycol, 3400 Da, Nektar, San Carlos, Calif.) was added to fibrinogen(Sigma-Aldrich, St. Louis, Mo.) in a concentration ratio of 1:10,BTC-PEG-BTC: Fibrinogen, in tris-buffered saline (TBS), pH 7.8, andincubated for 20 minutes at 37° C. An equal volume of thrombin(Sigma-Aldrich, St. Louis, Mo.) in 40 mM CaCl₂; and a finalconcentration of 100 U/ml was added and incubated for 10 minutes at 37°C. The resulting gels were then rinsed with TBS (pH 7.8) to removeunbound free BTC-PEG-BTC. To prepare ASC-seeded gels, cells of atdifferent concentrations (5000-50000/gel) were added to PEG-fibrinogenmixture before the initiation of gelation with thrombin. The cell-gelmixture was placed in a 12 well plate and incubated at 37° C. for 10minutes. After complete gelation, the PEGylated fibrin gels were washedtwice with HBSS and incubated with α-MEM (alpha minimal essential media)supplemented with 10% FBS, antibiotic-antimycotic (100 U/ml ofPenicillin G, 100 μg/ml streptomycin sulfate and 0.25 μg/ml AmphotericinB) and 2 mM Lglutamine (Invitrogen, Carlsbad, Calif.), in a 5% CO2humidified incubator at 37° C.

Morphological Analysis and Viability of ASC in PEGylated Fibrin Gel

ASC seeded at different concentrations (5000-50000 cells) in PEGylatedfibrin gel were observed and photomicrographs were taken at differenttime points (1, 3, 5 and 7 days) using an Olympus IX71 invertedmicroscope equipped with reflected fluorescence system and DP71 digitalcamera (Olympus America Inc, Center Valley, Pa.). At similar time pointsgrowth media was removed and 50 μl MTT(3-(4,5-dimethylthiozole-2-yl)-2,5-diphenyltetrazolium bromide,Sigma-Aldrich, St. Louis, Mo.) solution (5 mg/ml) was added to each geland incubated for 5 hours in a 5% CO2 humidified incubator at 37° C.After incubation the MTT solution was removed and 500 μl ofisopropyl-acetone mixture (1:1) was added and allowed to incubate for 30minutes to solubilize and extract the formazan complex. The gel-solventmixture was then centrifuged at 2700×g for 10 minutes and thesupernatant was collected and added to individual wells of a 24 wellplate. Absorbance of the supernatants and isopropyl alcohol-acetonemixture (reagent blank) was measured at 570 nm with 630 nm as referenceusing Molecular Devices Spectramax M2 Microplate Reader (MolecularDevices, Sunnyvale, Calif.). The cell number associated with PEGylatedfibrin gel was determined relative to the standard absorbance valueobtained from known numbers of viable ASC.

Immunocytochemical Analysis of ASC Seeded PEGylated Fibrin Gels

Immunostaining of ASC in PEGylated fibrin gels. Before cryosectioning,gels (day 11) were cryopreserved using gradient sucrose cryopreservationtechnique. Briefly, the gels were washed with HBSS (twice, 5 minutes),fixed with 4% paraformaldehyde (PFA, EMS, Hatfield, Pa.) treatedserially with increasing concentrations of sucrose (from 5% and 20%) andthen incubated overnight with 20% sucrose at 4° C. The sucrose treatedgels were embedded in a 20% Sucrose-Histoprep™ (Fisher, Pittsburgh, Pa.)mixture (2:1) and flash frozen. Sections, 10-12μm thick, were cut usinga cryostat (Leica Microsystems, Nussloch, GmbH), washed with sterileHBSS and fixed with 4% PFA for 20 minutes. Non specific Fc receptormediated blocking sites were blocked by incubating the sections for 40minutes—1 hr with 1% BSA (bovine serum albumin) in HBSS containing 0.01%Triton X 100 and washed twice (5 minutes) with HBSS. To assess theendogenic immunophenotype, sections were stained with anti rat CD31(PECAM-1, 8 μg, R&D Systems, Minneapolis, Minn.) and von Willebrandfactor (vWF, 10 μg/ml, Millipore, Billerica, Mass.) specific monoclonalprimary antibodies. For identifying pericyte immunophenotype, ratspecific monoclonal antibodies specific to Chrondroitin sulfateproteoglycan (NG2, 20 μg/ml, Millipore, Billerica, Mass.), plateletderived growth factor receptor beta (PDGFRβ, 10 μg/ml, R&D Systems,Minneapolis, Minn.) and alpha smooth muscle actin (α-SMA, 8 μg/ml,Abcam, Cambridge, Mass.) antibodies were used. The sections weresubjected to single or double immunofluorescent staining by incubatingwith a monoclonal primary antibody or mixture of two antibodies targetedtowards two different antigens at 4° C. overnight. Following incubationof unconjugated primary labeled antibodies, sections were washed twice(5 minutes) with HBSS and incubated with 5 μg/ml host species specificAlexa fluor 488 and/or Alexa fluor 594 secondary antibodies (Invitrogen,Carlsbad, Calif.) for 45 minutes at 4° C. Finally, the sections werewashed twice (5 minutes) and nuclei stained with Hoechst 33342(Invitrogen, Carlsbad, Calif.). Non-specific fluorescence was determinedusing sections incubated with respective fluorophore labeled secondaryantibodies.

Fluorescent and confocal microscopic morphological analysis.Epifluorescence of cells and gel sections were observed using Olympus Dminverted microscope equipped with reflected fluorescence system (OlympusAmerica Inc, Center Valley, Pa.). Photomicrographs were taken using DP71digital camera and image overlay was carried out using DP controllerapplication software. Three-dimensional images, were taken using anOlympus FV-500 Laser Scanning Confocal Microscope (Olympus AmericaInc.), equipped with three channel detection system for fluorescence, adifferential interference contrast image (DIC) laser light source andZstepper motor. The three dimensional stereoscopic images and movie weregenerated from a series of Z-stacked photomicrographs around the Z-axisusing Fluoview and Tiempo Ratio Imaging software and final imagesprocessed using Image J software (image processing and analysis in Java,NIH, Bethesda, Md.).

RNA Isolation and Real Time Polymerase Chain Reaction (RT-PCR)

Total RNA from ASC in PEGylated fibrin gel at 1,3,5,7 and 11 days wereisolated using Trizol LS reagent (Invitrogen, Carlsbad, Calif., USA)with modifications. Gels were rinsed with HBSS and carefully removedfrom the culture well. Four gels from each time were pooled together,minced, 16 ml of Trizol LS reagent was added and incubated for 10-15minutes in ice. Following incubation 8 ml of chloroform was added, mixedand the aqueous phase separated by centrifugation. The RNA was thenpurified using mini spin columns. The concentration and quality of thepurified RNA was determined at OD260/280 using a NanoDrop spectrometer(Nanodrop Technologies, Inc., Wilmington, Del.). Complementary DNA wassynthesized from 150 ng of total RNA, in duplicate, using SuperScript™III first strand synthesis supermix with oligo-dT primers (Invitrogen,Carlsbad, Calif., USA). A control lacking the RNA sample was synthesizedto detect the random production of cDNA through contaminants.Oligonucleotide primer sequences specific to endothelial (CD31 and vWF)and pericyte markers (NG2 and PDGFRβ) were purchased from SA Biosciences(Frederick, Md.). Master mixes containing 200 nM of forward and reverseprimers with SYBR® GreenER™, qPCR supermix (Invitrogen, Carlsbad,Calif.) and the synthesized cDNA were added to appropriate wells. RT-PCRwas carried out using a Bio-Rad CFX96 thermal cycler system (Bio-Rad,Hercules, Calif.). mRNA expression levels were normalized toglyceraldehye-3-phosphate dehydrogenase (GAPDH). Fold increase inexpression levels for each endogenic and pericyte specific gene wasnormalized to the expression levels of control passage 2 ASC. Foldincrease in expression levels for each gene was determined by 2-ΔΔCTmethod.

Impregnation of ASC Loaded Chitosan Microspheres in PEGylated Fibrin andCollagen Gels

Loading ASC into chitosan microspheres. Chitosan microspheres (CSM) wereprepared by water in oil emulsification process along with an ioniccoacervation technique using our previous described protocol. PreparedCSM were sterilized using absolute alcohol and washed (×3) with sterilewater to remove residual salts. ASC were loaded into CSM at 10000cells/mg using our culture insert technique as previously described.Before culturing ASC in CSM, the cells were cytoplasmically labeled withQuantum dot (Qdot) nanocrystals 565 using Qtracker cell labeling kit(Invitrogen, Carlsbad, Calif., USA). Cells were labeled according tomanufacturer's instructions, briefly; 2 μl of labeling solutioncontaining 10 nM of Qdots was incubated for 5 minutes at 37° C. and tothis solution 200 μl of MesenPRO media was added and vortexed. To thissolution mixture 1 ml of cell suspension (1×106 cells/ml) was added andincubated for 45 minutes at 37° C., 5% CO2. Following incubation labeledcell suspension was diluted with MesenPRO media to a final concentrationof 5×104 cells/200 μl and seeded over sterilized CSM (5 mg), spread overculture insert of 8 μm pore size membrane (24-well format, BD Falcon,Franklin Lakes, N.J.) and incubated for 24 hours in a humidifiedincubator at 37° C. and 5% CO2.

Impregnation procedure. ASC (with and without Qdot label) loaded CSM (5mg) were collected and mixed with PEGylated fibrin gel matrix (preparedas described earlier). The PEGylated fibrin-ASC-CSM mixture was added toa 12 well plate and incubated for 10 minutes at 37° C. In anotherexperimental setup ASC (with and without Qdot label) loaded CSM (5 mg)were collected and impregnated into collagen type I gels following ourprevious procedure. Briefly, type 1 collagen (5 mg/ml, Travigen,Gaithersburg, Md.) from rat tail tendon was fibrillated by adjusting thepH to 6.8-7.0 using 100 μl of Dulbecco's phosphate buffered saline(DPBS) and 23 μl of 1N NaOH. The fibrillated collagen-ASC-CSM mixturewas added to a 12 well plate and incubated for 30 minutes at 37° C.Following complete gelation both the gels (PEGylated fibrin and collagengels) were incubated at 37° C., 5% CO2. Release of cells was observedfor 8 days in case of PEGylated fibrin gels, while in collagen gelscells were observed for 12 days and light microscopic pictures weretaken at different days using Olympus IX71 inverted microscope equippedwith reflected fluorescence system. To track cells and show theirrelease into the gels fluorescence micrographs were taken on day 6 inboth the gels.

Development of Bilayered PEGylated Fibrin—(ASC-CSM)—Collagen GelConstructs

To develop the bilayer construct, PEGylated fibrin gel was prepared aspreviously described and added to a 6 well culture insert. Over thesurface of the PEGylated fibrin gel 5mg of ASC-loaded chitosanmicrospheres (10000 cells/mg) suspended in culture media (2000 wasseeded onto the gel. After the microsphere have settled over the gel,fibrillated type 1 collagen, prepared as previously described wascarefully applied over the PEGylated Fibrin—(ASC-CSM) platform beforegelation. After which the whole construct was placed for 30 minutes at37° C. to achieve complete gelation of collagen matrix. The finalbilayered construct consisted of PEGylated Fibrin—(ASC-CSM)—Collagen gelmatrix, with collagen gel on the top surface, PEGylated fibrin gel onthe bottom and the ASC loaded CSM sandwiched in the interface. Theentire bilayered construct was incubated at 37° C., 5% CO2 for 12 days,during which cells released into the gels, were observed andphotomicrographs were taken at different days to assess the morphologyof the released cells into the gel matrix.

Results Undifferentiated ASC

The phenotype of undifferentiated ASC has been described with respect tocell surface marker expression measured with FACS. These cells arepositive for CD49d, CD54, CD71, CD90 and STRO-1. Prior to theutilization of a particular cell population the positive expression ofthese five markers was confirmed using immunocytochemical staining Anexample result for the cell populations used in this study is shown inFIG. 13.

ASC Growth Characteristics within PEGylated Fibrin

Much like bone marrow-derived MSCs, ASC demonstrate the ability toproliferate and express a characteristic phenotype within PEGylatedfibrin gels. FIG. 14 shows the dependency of cell seeding density andculture time on the resulting cell morphology. ASC began to exhibitcellular extensions by day 3. These extensions were more pronounced incultures with >10,000 cells/ml. Over time the cellular extensionsprogressed with the formation of dense multicellular networks. By day 7,ASC at all seeding densities demonstrated extensive network formationwhich was greatest at the highest cell density. Proliferation wasassessed over the same timecourse using the MTT assay. (FIG. 5)Proliferative activity increased over the seven day study for allseeding densities and was dependent on the initial density.

ASC Phenotype and Genotype within PEGylated Fibrin

The endothelial cell markers, CD31 and vWF were used to establish theidentity of cells expressing an endothelial cell genotype and phenotype.RT-PCR demonstrated that over the 11 day timecourse, there was adramatic upregulation of endothelial cell markers relative to thehousekeeping gene. Specifically, CD31 was upregulated 25 fold overcontrols while vWF was up 42 fold over controls. (FIG. 15) Theimmunohistochemical staining confirmed the presence of the expressedprotein for both CD31 and vWF. (FIG. 7A-7D) Confocal images of stainedsections confirm that both markers are expressed on multicellularnetworks generated from day 11 samples. What was demonstrated is thatthe CD31 is more closely associated with the cell nucleus than the vWF.This may be due to the fact that CD31 is expressed on endothelial cellmembranes, where vWF may be secreted from the cell and maintained withinthe fibrin network. The pericyte markers, NG2, PDGFRβ and α-smoothmuscle actin were used to track the differentiation of ASC towards apericyte, or mural cell, phenotype. RT-PCR after 11 days in culturedemonstrated that the markers, NG2 and PDGFRβ, were upregulated by 6fold and 9 fold, respectively, relative to controls. It is important tonote here that undifferentiated ASC also express a basal level of PDGFRβwhich was approximately 5 fold greater than controls. This valuedeclined as the culture progressed reaching a minimum at day 7 prior toan increase at day 11. Immunohistochemistry revealed that multicellularnetworks at day 11 exhibited expression of both NG2 (FIG. 7E-7H) andα-SMA (FIG. 7I-7L). Further, a 3-D Z-stack animation was created fromsections stained with vWF and α-SMA individually to observe the tubearchitecture formed in the fibrin gels. The co-localization of thesemarkers typically demonstrated that α-SMA occupied a position on theexterior of the tube relative to vWF. This indicated that the cellpopulations expressing endothelial and pericyte markers are separatewith the pericyte markers occupying a pericellular position within thegrowing network.

ASC Migration from Chitosan Microspheres

As shown in FIGS. 7 and 16, cells that had been seeded onto chitosanmicrospheres were able to migrate though either PEGylated fibrin (FIG.16A-C) or collagen (FIG. 16D-F). Migration was seen in both gels asearly as day 2 after seeding. Migration and/or proliferation continuedthroughout the times monitored (day 8 for PEGylated fibrin and day 12for collagen). ASC migrating into the PEGylated fibrin demonstrated thecharacteristic tubular morphology as seen in the gel matrix alone, whileASC migrating through the collagen matrix had a spindleshapedmorphology.

When ASC were pre-labeled with Qdot 565 nanocrystals and visualizedafter 6 days in culture, the labeled cells could be clearly seen asdistinct from the chitosan microspheres. The fluorescent images as wellas the brightfield overlay for migration into both PEGylated fibrin(FIG. 17A-C) and collagen (FIG. 17D-F) are shown. This result providesevidence that the ASC are able to migrate from the embedded microspheresand into either collagen or PEGylated fibrin.

Matrix-Based Morphology of ASC

FIG. 17 consists of a series of light microscopy images over an 11 daytimecourse as ASC grow out of chitosan microspheres into either collagenor PEGylated fibrin. The cells that had been cultured on the surface ofmicrospheres were “sandwiched” between the two different gel layers.This type of experimental setup allowed for the independentinvestigation of the effects that the matrix environment had on cellmigration and differentiation. Cells were clearly able to leave themicrosphere surface and migrate into either the collagen gel or thePEGylated fibrin. Cells in both gel layers were evident from day 3 untilthe end of the culture period. The morphology of the migrated ASC weredramatically different in the two gel layers. In the collagen gels, thecells exhibited a spindle-shaped morphology similar to what was seen inthe collagen gel layer by itself In the PEGylated fibrin gels, the cellsdemonstrated multicellular tubular networks analogous to those in thePEGylated fibrin layer alone. In a number of the figures, it can beclearly seen that the same microsphere population is shown either fromthe underside (PEGylated fibrin, FIG. 18B, D and F) or the top side(collagen, FIG. 18A, C and E). This indicates the close proximity of thetwo cell phenotypes as well as the fact that cells on the same bead canexhibit two distinct phenotypes. The cells in the PEGylated fibrin wereable to form extended networks that spanned the dimensions of theacquired image. This result provides evidence for the purelymatrix-driven differentiation of ASC in either collagen or PEGylatedfibrin.

Therefore, the present invention is well adapted to attain the ends andadvantages mentioned as well as those that are inherent therein. Itshould be understood, however, that the description of specific exampleembodiments is not intended to limit the invention to the particularforms disclosed, but on the contrary, this disclosure is to cover allmodifications and equivalents as defined by the appended claims. Whilenumerous changes may be made by those skilled in the art, such changesare encompassed within the spirit of this invention as illustrated, inpart, by the appended claims.

What is claimed is:
 1. A laminar construct comprising: a synthetichydrogel matrix comprising at least a first synthetic hydrogel layer anda second synthetic hydrogel layer, wherein the first synthetic hydrogellayer comprises at least one material selected from the group consistingof fibrin, PEGylated fibrin, hyaluronic acid, and any combinationthereof and wherein the second synthetic hydrogel layer comprises atleast one material selected from the group consisting of collagen I,collagen II, collagen III, collagen IV, collagen V, fibronectin,tenascin, vitronectin, glycosaminoglycans, and any combination thereof;and a plurality of mesenchymal stem cells positioned between the firstsynthetic hydrogel layer and the second synthetic hydrogel layer.
 2. Theconstruct of claim 1 wherein the plurality of mesenchymal stem cellscomprise adipose derived stem cells.
 3. The construct of claim 1 whereinthe first synthetic hydrogel layer comprises PEGylated fibrin.
 4. Theconstruct of any of claims 1-3 wherein the second synthetic hydrogellayer comprises collagen I.
 5. The construct of claim 1 wherein thesynthetic hydrogel matrix is free of soluble growth factors.
 6. Theconstruct of claim 1 wherein the plurality of mesenchymal stem cells areon microcarriers.
 7. A laminar construct comprising: a synthetichydrogel matrix comprising at least a first synthetic hydrogel layer anda second synthetic hydrogel layer, wherein the first synthetic hydrogellayer comprises at least one material selected from the group consistingof fibrin, PEGylated fibrin, hyaluronic acid, and any combinationthereof and wherein the second synthetic hydrogel layer comprises atleast one material selected from the group consisting of collagen I,collagen II, collagen III, collagen IV, collagen V, fibronectin,tenascin, vitronectin, glycosaminoglycans, and any combination thereof;and a plurality of mesenchymal stem cells positioned within the firstand second synthetic hydrogel layers.
 8. The construct of claim 7wherein the plurality of mesenchymal stem cells comprise adipose derivedstem cells.
 9. The construct of claim 7 wherein the first synthetichydrogel layer comprises PEGylated fibrin.
 10. The construct of any ofclaims 7-9 wherein the second synthetic hydrogel layer comprisescollagen I.
 11. The construct of claim 7 wherein the synthetic hydrogelmatrix is free of soluble growth factors.
 12. A laminar constructcomprising: a synthetic hydrogel matrix comprising at least a firstsynthetic hydrogel layer and a second synthetic hydrogel layer, whereinthe first synthetic hydrogel layer comprises at least one materialselected from the group consisting of fibrin, PEGylated fibrin,hyaluronic acid, and any combination thereof and wherein the secondsynthetic hydrogel layer comprises at least one material selected fromthe group consisting of collagen I, collagen II, collagen III, collagenIV, collagen V, fibronectin, tenascin, vitronectin, glycosaminoglycans,and any combination thereof; and a plurality of cells comprising adermal fibroblast and a blood vessel cell, wherein the plurality ofcells are positioned between the first synthetic hydrogel layer and thesecond synthetic hydrogel layer.
 13. The construct of claim 12 whereinthe first synthetic hydrogel layer comprises PEGylated fibrin.
 14. Theconstruct of claim 12 or 13 wherein the second synthetic hydrogel layercomprises collagen I.
 15. The construct of claim 12 wherein thesynthetic hydrogel matrix is free of soluble growth factors.